Polymeric biomaterials derived from monomers comprising hydroxyacids and phenol compounds and their medical uses

ABSTRACT

The present invention provides new classes of phenolic compounds derived from hydroxyacids and tyrosol or tyrosol analogues, useful as monomers for preparation of biocompatible polymers, and the biocompatible polymers prepared from these monomeric hydroxyacid-phenolic compounds, including novel biodegradable and/or bioresorbable polymers. These biocompatible polymers or polymer compositions with enhanced bioresorbabilty and processibility are useful in a variety of medical applications, such as in medical devices and controlled-release therapeutic formulations. The invention also provides methods for preparing these monomeric hydroxyacid-phenolic compounds and biocompatible polymers.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims the benefit of priority under 35 USC 119(e) ofU.S. Provisional Application No. 61/863,216 filed on Aug. 7, 2013, theentire disclosure of which is incorporated herein by reference.

FIELD OF THE INVENTION

The present invention relates to new classes of monomeric phenolcompounds useful for preparation of biocompatible polymers, andbiocompatible polymers prepared therefrom, including novel biodegradableand/or bioresorbable polymers. These polymers, while not limitedthereto, may be adapted for radio-opacity and are useful for medicaldevice applications and controlled release therapeutic formulations.

BACKGROUND OF THE INVENTION

The rapidly evolving field of bioengineering has created a demand for adiverse library of different types of polymers offering a wide varietyof choice of physical, mechanical, chemical and physiologicalproperties. It is desirable that libraries of many different materialsbe available so that the specific polymer properties can be optimallymatched with the requirements of the specific applications underdevelopment.

Examples of polymers suitable for various bioengineering applicationsinclude those described in U.S. Pat. Nos. 5,099,060; 5,665,831;5,916,998 and 6,475,477, along with the polymers described in U.S.Patent Publication Nos. 200610024266 and 2006/0034769. There arenumerous applications in which it is considered desirable for animplanted medical device to maintain its integrity and performancecharacteristics for extended periods of time, even under demandingmechanical conditions such as repeated mechanical flexure. Although manytypes of bioresorbable and/or biodegradable polymers are known, in mostof these polymers dipbenolic monomers are prepared by linking twosuitably protected tyrosine molecules or tyrosine analogs via an amidelinkage. These amide linkages do not degrade hydrolytically underphysiological conditions and therefore the monomers which have lowsolubility in water, dissolve very slowly. Further, due to hydrogenbonding of amide hydrogen the melt viscosity of the polymers derivedfrom these monomers is very high, which makes thermal processing moredifficult. In addition, bioresorbtion and/or biodegradation tend toalter mechanical properties in unpredictable was that are notnecessarily linearly related to each other.

Thus, there continues to be a need for blocompatible polymers havingdesirable bioresorbability and biodegradability good processibilityunder thermal conditions, as well as the appropriate level of mechanicalstructural support necessary for medical device applications. Thereremains a need for nontoxic polycarbonates, polyarylates and otherpolymers having a moderate rate of bioerosion, suitable for use astissue-compatible materials for biomedical uses,

SUMMARY OF THE. INVENTION

The present invention addresses the foregoing need by providing newmonomers useful for the preparation of the desired biocompatiblepolymers and various types of such polymers useful for making theimplantable medical devices.

Hydroxyacid-phenolic compounds, such as tyrosyl lactates, tyrosylglycolates and related, compounds are a new class of diolmonomerimacromers in which one of the hydroxy groups is aromatic(phenolic) and the other is aliphatic. These can be prepared, forexample, by using tyrosol as the initiator for the ring openingreactions of cyclic reaction partners such as lactides, lactones andcyclic carbonates. Using such monomers as co-monomers together withother diphenolic monomers in condensation polymerizations providesrigidity and mechanical strength that is lacking in aliphatic-derivedmonomers and also allows degrees of flexibility and degradabilly thatare desirable in bioresorbable polymers for medical uses.

The present invention broadly relates to hydroxy acid-phenolic monomersand bioderodible polymers synthesized using such monomers. In variousembodiments, the hydroxyacid-phenolic monomers are derived from tyrosoland/or related analogs. In particular, one preferred aspect of thepresent invention is directed to bioerodible polycarbonates andpolyarylates derived from the naturally occurring4-(2-hydroxylethyl)phenol or “tyrosol”) and phosgene and/orbiocompatible dicarboxylic acids.

One aspect the present invention is directed to biocompatible polymerscomprising a repeating structural unit of the Formula

wherein

y1 is 0, 1, 2, 3, or 4;

X¹ is bromine (Br) or iodine (I):

X² and X³ are independently selected from O, S and NR, where R is for orlower alkyl;

R¹ is selected, from the group consisting of linear or branched C₁-C₁₂alkylene;

A is selected from the group consisting of linear or branched C₁-C₂₄alkylene;

R² is selected from the group consisting of linear or branched C₁-C₂₄alkylene;

n1 and n2 are independently numbers from 0 to 100, and are averagevalues which can be fractional, where the sum of n1 and n2 is at least1;

p is zero or 1 and

A¹ is a linking group selected from:

wherein R⁸ selected from a bond, C₁-C₃₀ alkylene, C₁-C₃₀ alkenylene,C₂-C₃₀ alkenylene, C₂-C₃₀ alkynylene; C₁-C₃₀ heteroalkylene, C₂-C₃₀heteroalkenylene, C₂-C₃₀ heteroalkynylene, C₇-C₃₀ heteroalkylarylene,beteroalkenylarylene, C₈-C₃₀ heteroalkynylarylene, C₇-C₃₀ alkylarylene,alkenylarylene, alkynylarylene, and C₂-C₃₀ heteroarylene; and

R⁹ and R¹⁰ are each independently selected from H, C₁-C₃₀ alkyl,heteroalkyl, C₂-C₃₀ alkenyl, alkynyi, heteroalkenyl, and C₂-C₃₀heteroalkynyl:

wherein said alkyl and alkylene can be substituted with one or more ofhydroxy, alkoxy, halogen, nitro, cyano, CO₂R, where R is defined above,phenyl, aryl, heteroaryl, cycloaikyl, mercapto, or alkylthio.

In a preferred embodiment R² is CH—R³, where R³ is selected fromhydrogen and C₁-C₂₃ alkyl.

Examples of the inventive polymers include polycarbonates, polyarylates,polyiminocarbonates, polyphosphazenes and polyphosphoesters.

Another aspect the present invention is direct-d to hydroxyacid-phenolcompounds of formula:

wherein

y1 is 0, I, 2, 3, or 4;

X¹ is bromine (Br) or iodine (i)

X² and X³ are independently selected from O, S and NR, where R is H orlower alkyl;

R¹ is selected, from the group consisting of linear or branched C₁-C₁₂alkylene;

A is selected from the group consisting of linear or branched C₁-C₂₄alkylene;

R² is selected from the group consisting of linear or branched C₁-C₂₄alkylene;

n1 and n2 are independently numbers from 0 to 100, and are averagevalues which can be fractional, where the sum of n 1 and n2 is at least1;

p is zero or 1; and

wherein said alkyl and alkylene can be substituted with one or more ofhydroxy, alkoxy, halogen, nitro, cyano, CO₂H, Co₂-lower alkyl, phenyl,aryl, heteroaryl, cycloalkyl, mercapto, or alkylthio.

In a preferred embodiment, R² is CH—R³, where R³ is selected fromhydrogen and C₁-C₂₃ alkyl.

Yet another aspect of the invention is directed to polymer compositionscomprising a biocompatible polymer described herein.

One aspect of the invention is direct to medical devices comprising abiocompatible polymer described herein. In a preferred embodiment, themedical device is a stent.

Another aspect of the invention is direct to inventive biocompatiblepolymers further comprisintt a macromeric recurring unit, or

a recurring unit of the torr —[B-A¹—]wherein B is —O—((CHR)_(p)—O)_(q)—; each R is independently H or C₁ toC₃ alkyl; p and q are each independently an integer in the range of fromto 100; and A¹ is as defined above, independently from any other A¹; ora tyrosol recurring unit characterized by the formula:

wherein A¹ is as defined above, independently from any other A¹; or aniodinated tyrosol recurring unit characterized by the formula:

wherein Al is as defined above, independently from any other A¹; or aniodinated recurring unit characterized by the formula:

wherein A¹ is as defined above, independently from any other A¹.

These and other embodiments are described in greater detail below.

DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS

To meet the need. of versatile moldable biodegradable and biocompatiblepolymers made using relatively nontoxic monomeric starting materials,the present application describes a variety of such monomers andpolymers prepared from these monomers.

One aspect of the invention is directed to a biocompatible polymer,comprising a recurring unit of formula:

wherein

y1 is 0, 1, 2, 3, or 4; preferably 0, 1 or 2; or preferably 1 or 2; orpreferably 2;

X¹ is a halogen; preferably bromine (Br) or iodine (i); more preferablyiodine;

X² and X³ are independently selected from O, S and NR, where R is H orlower alkyl; preferably X² and X³ are O;

R¹ is selected from the group consisting of linear or branched C₁-C₁₂alkylene; preferably C₁-C₆ alkylene; more preferably C₁-C₂₄ alkylene;most preferably C₂ alkylene;

A is selected from the group consisting of linear or branched C₁-C₂₄alkylene; preferably C₁-C₁₂ alkylene; more preferably C₁-C₆ alkylene;still more preferably C₂-C₄ alkylene; most preferably C₃ alkylene;

R² is selected from the group consisting of linear or branched C₁-C₂₄alkylene; preferably C₁-C₁₂ alkylene; more preferably C₁-C₆ alkylene;still more preferably C₁-C₄ alkylene; most preferably C₁-C₂ alkylene;

n1 and n2 are independently numbers from 0 to 100, preferably 0 to 20,more preferably 0 to 10, still more preferably 0 to 5, most preferably 0to 2, and are average values which can be fractional., where the sum ofn1 and n2 is at least 1;

p is zero or 1; and

A¹ is a linking group selected from:

wherein R⁸ is selected from a bond, C₁-C₃₀ alkylene, C₂-C₃₀ alkenylene,alkynylene; C₁-C₃₀ heteroalkylene, heteroalkenylene, C₂-C₃₀heteroalkynylene, C₇-C₃₀ heteroalkylarylene, beteroalkenylarylene,heteroalkynylarylene, C₇-C₃₀ alkylarylene, alkenylarylene, C₈-C₃₀alkynylarylene, and C₂-C₃₀ heteroarylene; and

R⁹ and R¹⁰ are each independently selected from H, C₁-C₃₀ alkyl, C₁-C₃₀heteroalkyl, C₂-C₃₀ alkenyl, C₂-C₃₀ alkynyl, C₂-C₃₀ heteroalkenyl, andC₂-C₃₀ heteroalkynyl;

wherein said alkyl and alkylene can he substituted with one or more ofhydroxy, alkoxy, halogen, nitro, cyano, CO₂R, where R is defined above,phenyl, aryl, heteroaryl, cycloalkyl, mercapto, or alkylthio.

In one embodiment R¹ is C₁-C₄ alkylene. Preferably R¹ is —CH₂CH₂—.

In another embodiment, A¹ is carbonyl (C═O). In another embodiment A¹ isderived from a diacid and has the structure (O═C)—R⁸—(CO). with R⁸ asdefined above.

In one embodiment, n1 is zero and n2 is an average value between 0.5 and6. Preferably n2 is an average value between I and 2.

In another embodiment the biocompatible olymer comprises recurring unitof formula:

having the phenolic attachment at the para position of the phenyl ring,where the variables are defined above.

In another embodiment the biocompatible polymer comprises recurring unitof formula:

wherein R³ is selected from the group consisting of hydrogen and linearor branched C₁-C₂₃ alkyl, and the other variables are defined above. Ina preferred embodiment the recurring unit is of formula:

having the phenolic attachment at the para position of the phenyl ring,where the variables are defined above. Preferably R² is hydrogen ormethyl. In a preferred embodiment, n2 is greater than zero and R³ ismethyl and the subunit is derived from L-lactic acid, in anotherpreferred embodiment n2 is greater than zero and R³ is methyl and thesubunit is derived from D-lactic acid, In another preferred embodiment,n2 is greater than zero and R³ is methyl and the subunit is derived fromD,L-lactic acid.

In another aspect of the invention, the biocompatible polymer furthercomprises a recurring unit of the formula:

—[B-A¹-]

wherein B is —O—((CHR)_(p)—O)_(q); each R is independently H or C₁ to C₃alkyl; p and q are each independently an integer in the ranee of from to100; and A¹ is as defined above, independently from any other A¹.Preferably R is H and p is 2, providing poly(ethylene glycol) (PEG)recurring unit.

In another aspect of the invention, the hiocompatible polymer furthercomprises a recurring unit of the formula:

wherein A¹ is as defined above, independently from any other A¹.

In another aspect of the invention, the hlocomparible polymer furthercomprises a recurring unit of the formula:

wherein A¹ is as defined above, independently from any other A¹.

In another aspect of the invention, the biocompatible polymer furthercomprises a recurring unit of the formula:

wherein A¹ is as defined above, independently from any other

A further aspect of the invention is directed to hydroxyacid-phenolcompounds of formula:

wherein

-   -   y1 is 0, I, 2, 3, or 4; preferably 0, 1 or 2; or preferably 1 or        2; or preferably 2;    -   X¹ is a halogen; preferably bromine (Br) or iodine (I); more        preferably iodine;    -   X² and X³ are independently selected from O, S and NR, where R        is H or lower alkyl; preferably X² and X³ are O;    -   R¹ is selected from the group consisting of linear or branched        C₁-C.₁₂ alkylene; preferably C₁-C₆ alkylene; more preferably        C₁-C₄ alkylene; most preferably C₂ alkylene,

A is selected from the group consisting of linear or branched C₁-C₂₄alkylene: preferably C₁-C₁₂ alkylene; more preferably C₁-C₆ alkylene;still more preferably C₂-C₄ alkylene; most preferably C₃ alkylene;

-   -   R² is selected from the group consisting of linear or branched        C₁-C₂₄ alkylene; preferably C₁-C₁₂ alkylene; more preferably        C₁-C₆ alkylene, still more preferably C₁-C₄ alkylene; most        preferably C₁-C₂ alkylene;    -   n1 and n2 are independently numbers from 0 to 100, preferably 0        to 20, more preferably 0 to 10, still more preferably 0 to 5,        most preferably 0 to 2, and are average values which can be        fractional., where the sum of n I and n2 is at least 1;    -   p is zero or 1; and    -   wherein said alkyl and alkylene can be substituted with one or        more of hydroxy, alkoxy, halogen, nitro, cyano. CO₂H, CO₂-lower        alkyl, phenyl, aryl, heteroaryl, cycloalkyl, mercapto, or        alkylthio.

In one embodiment n1 is zero and n2 is an average value of 2. In anotherembodiment X¹=I and y1=2. Preferably R¹ is —CH₂CH₂— (tyrosol).

In another aspect of the invention, the hydroxyacid-phenol has theformula;

where the phenolic attachment is at the para position of the phenylring, and the variables are defined above.

In a further aspect of the invention, the hydrOxyacid-pheriol compoundhas the formula:

wherein R³ is selected from the group consisting of hydrogen and linearor branched C₁-C₂₃ alkyl, and the other variables are defined as above.Preferably the hydroxyacid-phenol compound has the formula:

where the phenolic attachment is at the para position oldie phenyl ring,and the variables are defined above.

In a preferred embodiment, R³ is hydrogen or methyl. In one preferredembodiment, n2 is greater than zero and R³ is methyl and the subunit isderived from L-lactic acid, in another preferred embodiment, n2 istreater than zero and R³ is methyl and the subunit is derived fromD-lactic acid. In still another preferred embodiment, n2 is greater thanzero and R is methyl and the subunit is derived from D,L-lactic acid.

One aspect of the invention is directed to polymer compositionscomprising a biocompatible polymer described herein.

Another aspect of the invention is directed to a medical devicecomprising a biocompatible polymer described herein. In one embodiment,the medical device is a stem. The medical device can further comprise abiologically active compound. The biologically active compound can beselected from the group consisting of a chemotherapeutic agent, anon-steroidal anti-inflammatory, a steroidal anti-inflammatory, and awound healing agent.

In one particular aspect this invention provides hydro.xyacid-phenolicmonomers derived from a hydroxyalk.ylphenol having a generic structureof Formula (IV):

wherein R¹ is defined as above. R¹ is preferably C₁-C₁₂ alkylene, e.g.,C₁-C₄ alkylene. More preferably R¹ is ethylene (—CH₂—CH₂—). Mostpreferably, the hydroxyalkyl-phenol is 4-(2-hydroxyethyl)phenol or2-(4-hydroxyphenyl)ethanol, also known as “tyrosol”, having thefollowing structure:

which is a natural product present in olive oil and white wine and hasbeen shown to have both antioxidant and cardio-protective properties.The phenyl ring of tyrosol can be halogenated, and those skilled in theart will understand that teachings herein regarding tyrosol can beapplied to such halogenated forms as well. Tyrosol can be converted intoa hydroxyacid-phenolic monomer in several ways. It can be esterifiedwith hydroxyacids, particularly alpha-hydroxyacids, to form a phenolicmonomer with an ester linkage. These monomers can be introduced intopolymers to control chain flexibility, as needed. Those skilled in theart will appreciate that use of ring halogenated compounds (e,g.,halogenated tyrosol) provides the corresponding halogenated polymers.

The hydroxyacid-phenolic monomers described herein, can be polymerizedusing, phosgene to form polycarbonates, or polymerized with dicarboxylicacids to obtain polyarylates. The hydroxyacid-phenolic monomers can alsobe copolymerized with other co-monomers including diphenols such asdesaminotyrosyl tyrosine ethyl ester, DAT) and other dihydroxy compoundssuch as polyethylene glycol), polycaprolactone-diol, poly(trimethylenecarbonate), polyactide and/or polyglycolide. Suitable co-monomers aredisclosed in U.S. Pat. Nos. 8,252,887 and 8,476399, the disclosures ofwhich are incorporated herein by reference. The polymers can be maderadio-opaque by introducing halogen, in particular iodine and/or bromineatoms, on the phenyl rings, or on other suitable sites of the monomers.Other optionally halogenated phenolic alcohols can be used in place oftyrosol and other optionally halogenated hydroxy carboxylic acids can beused in place of glycolic acid and lactic acid.

In another aspect, the present invention provides a biocompatiblepolymer composition, comprising at least a first polymer component and asecond polymer component. In an embodiment, the first polymer componentcomprises a number (n) of first recurring units of thehydroxyacid-phenolic compounds as set forth above, and the secondpolymer component comprises recurring units having a formula selectedfrom the group consisting of the formula (IX), the formula (X), theformula (XI), and the formula (XII):

wherein X³, X⁴, X⁵, X⁷, X⁸, X⁹, X¹⁰, X¹¹, X¹² and X¹³ are independentlyselected from the group consisting of O, S and NR^(H), where R¹¹ isselected from hydrogen and an alkyl group containing from one to 30carbon atoms;

Ar¹ and Ar² are phenyl rings optionally substituted with from one tofour substituents independently selected from the group consisting of ahalogen, a halomethyl, a halomethoxy, a methyl, a methoxy, a thiomethyl,a nitro, a sulfoxide, and a sulfonyl;

R¹² and R¹³ contain from one to ten carbon atoms each and areindependently selected from the group consisting of an optionallysubstituted alkylene, an optionally substituted heteroalkylene, anoptionally substituted alkenylene, and an optionally substitutedheteroalkenylene;

g and h in formula (XII) are each independently integers in the range ofabout 1 to about 500; and

D and D¹ contain up to 24 carbon atoms and are independently selectedfrom the group consisting of an optionally substituted alkylene, anoptionally substituted heteroalkylene, an optionally substitutedalkenylene and an optionally substituted heteroalkenylene;

or D, X⁸ and X⁹ in formula (IX) are selected so that defines a hydroxylendcapped macromer, a mercapto endcapped macromer or an amino endcappedmacromer;

or D¹, X³ and X⁴ in formula (XI) are selected so that defines a hydroxylendcapped macromer, a mercapto endeapped macromer or an amino endcappedmacromer. These, as well as other suitable polymer components and/orpolymer phases are set fourth in U.S. patent application Ser. No.12/577,203, which is incorporated herein by reference.

In other aspects, the present invention provides copolymers thatcomprise any two or more of the recurring units described herein. Forexample, in an embodiment, the polymer comprises two Or more recurringunits selected from the group of recurring units represented by theformulae presented above. In another embodiment, the polymer comprisesat least two recurring units resulting from the polymerization of anytwo or more monomers described herein.

In other aspects of the invention, the polymer comprises a backbonewhich is not naturally occurring. Alternatively and/or additionally, thepolymer may comprise a backbone comprising at least one amino acidderivative.

A polymer comprising a recurring unit as described herein can becopolymerized with any number of other recurring units. In anembodiment, a polymer comprising a recurring unit of any one or more ofthe above formulae, further comprises a recurring unit of the formula(XIV):

—[B-A¹-]  (XIV),

wherein:

B in formula (XIV) is —O—((CHR)_(p)—O)_(q);

each R is independently H or C₁ to C₃, alkyl; p and q are eachindependently an integer in the range of from about I to about 100; and

A¹ is as defined above, independently from any other A¹.

In preferred embodiments, Formula (XIV) includes polyethylene glycol(PEG) recurring units (R═H and p=2), polyproplyene glycol (PPO)recurring units (p=2, and two adjacent R's H and CH₃, respectively)and/or poly(trimethylene carbonate) (PTMC) recurring units (R′H, q=1,p=3 and

In vivo, the polymer is expected to hydrolyze to release the originalhydroxyacid-phenolic compound and diacid (polyarylate) or CO ₂(polycarbonate), thus forming nontoxic degradation products, providedthat the monomeric starting materials are nontoxic. The toxicologicalconcerns associated with polyarylates are met by usinghydroxyacid-phenolic derived from tyrosol and dicarboxylic acids thatare either metabolites or highly biocompatible compounds.

Another aspect of the present invention provides molded articlesprepared from the polymers of the present invention.

Based on the foregoing, in certain embodiments of the biocompatiblepolymers described herein, A′ is a carbonyl group having a structure of

wherein the carbonyl group is derived from a phosgene starting material.This method is essentially the conventional method for polymerizingdiols into polyearbonates. Suitable processes, associated catalysts andsolvents are known in the art and are taught in, for example, Schnell,Chemistry and Physics of Polycarbonates, (Interscience, New York 1964),the teachings of which are incorporated herein by reference. Othermethods adaptable for use to prepare the poly-carbonate and otherphosgene-derived polymers of the present invention are disclosed in U.S.Pat. Nos. 6,120,491 and 6,475,477 the disclosures of which areincorporated by reference.

In another embodiment of the polymers described herein. A¹ is a grouphaving the structure:

which is a recurring unit derived from a dicarboxylic acid startingmaterial or monomer. When the monomer used to form the polymer is ahydroxyacid-phenolic compound, the hydroxyacid-phenol can be reactedwith an aliphatic or aromatic dicarboxylic acid in the carbodiimidemediated process disclosed by U.S. Pat. No. 5,216,115 using4-(dimethylamino)pyridiniuirt p-toluene sulfonate (DPTS) as a catalyst.The disclosure of U.S. Pat. No. 5,2.16,115 is incorporated by reference,and particularly for the purpose of describing such polymerizationmethods. This process forms polymers with —O—C(═O)—R⁸—C(═O)—O— linkages,may be selected so that the dicarboxylic acids employed as startingmaterials are either important naturally-occurring metabolites or highlybiocompatible compounds. Aliphatic. dicarboxylic acid starting materialstherefore include the intermediate dicarboxylic acids of the cellularrespiration pathway known as the Krebs Cycle. The dicarboxylic acidsinclude et-ketoglutaric acid, succinic acid, fumaric acid andoxaloacetic acid (R⁸ may be —CH₂—C(αO—, —CH₂—CH₂—, —CH═CH— and—CH₂—C(═O)—, respectively).

Yet another naturally occurring aliphatic dicarboxylic acid is adipicacid (R⁸ is —(CH₂)₄—), found in beet juice. Still another biocompatiblealiphatic dicarboxylic acid is sebacic acid (R⁸ is —(CH₂)₈—), which hasbeen studied extensively and has been found to be nontoxic as part ofthe clinical evaluation of poly(bis(p-carboxyphenoxy)propane-co-sebacicacid anhydride) by Laurencin et al., J. Biomed. Mater. Res., 24,14(53-S1 (1990).

Other biocompatible aliphatic dicarboxylic acids include oxalic acid (R⁸is a bond), malonic acid (R⁸ is —CH₂—), glutaric acid (R⁸ is —(CH₂)₃—),pimelic acid (R⁸ is —(CH₂)₅—), suberic acid (R⁸ is —(CH₂)₆—) and azelaicacid (R⁸ is —(CH₂)₇—). R⁸ can thus represent —(CH₂)_(n)—, where n isbetween 0 and 8, inclusive. Among the suitable aromatic dicarboxylicacids are terephthalic acid, isophthalic acid andbis(p-carboxy-phenoxy)alkanes such as bis(p-carboxy-phenoxy) propane.

Preferred polymers comprise a recurring unit as described herein.Preferred polymers can contain combinations of derivatives of structuralunits selected from dicarboxylic acids, halogenated e.g., iodinated orbrominated) derivatives of desaminotyrosykyrosine and poly(alkyleneglycols), which exhibit desirable physicomechanical and physicochemicalproperties that are consistent with their use in fabrication of medicaldevices, including stems. For example, the stents described inaccordance with preferred embodiments of the present invention: (a) aresufficiently radiopaque to be visible by conventional X-ray fluoroscopy;(b) are of sufficient strength to support medically relevant levels ofradial compression within an artery or surrounding tissue; and/or (c)have a desirable resorption profile that may be adjusted to account farthe needs of a range of applications requiring the presence of a stentfor different lengths of time or for the elution of therapeutics.

Halogenation of the aromatic rings may be accomplished as described inthe examples below, and by conventional methods as detailed in U.S. Pat.No. 6,475,477; herein incorporated in its entirety by reference andparticularly for the purpose of describing methods of halogenatingmonomers. Preferred polymers are sufficiently halogenated to render theresulting polymers radiopaque, e.g., y1 in any of the formulae describedherein may independently be 0, 1, 2, 3 or 4. Halogenation of aromaticrings is preferred. In an embodiment, y1 is at least one. Various othergroups within the polymer may also be halogenated.

Monomer and Polymer Syntheses

The hydroxyacid-phenolic monomers of the invention are advantageouslyprepared by the reaction of a hydroxyalkylphenol having a genericstructure of Formula (IV):

as described above, with a cyclic reaction partner preferably selectedfrom the group consisting of cyclic dimers of alpha-hydroxyacids,lactones and cyclic carbonates (see Examples). Preferably thehydroxyalkylphenol is tyrosol (R¹═CH₂CH₂, with phenolic OH in thepara-position). Cyclic dimers of alpha-hydroxyacids include, withoutlimitation, glycolide and lactide. The lactide can be L,L-lactide,R,R-lactide, L,R-lactide, or racemic lactide, since the precursor lacticacid contains a chiral carbon atom. We have observed that reaction oftyrosol, and related hydroxyalkylphenols, with such cyclic reactionpartners proceeds by exclusive reaction of the aliphatic hydroxyl groupto ring-open the cyclic alpha-hydroxyacid dimer, lactone or cycliccarbonate, thereby providing monomers which endow their correspondingpolymers with desirable physicochemical and degradation properties, videinfra.

The polymers described herein may be synthesized by various conventionalreactions known in the art.

For example, the hydroxyacid-phenolic monomer compounds can be reactedwith aliphatic or aromatic dicarboxylic acids in a carbodimidmediateddirect polyesterification using DPTS as a catalyst to form aliphatic oraromatic polyalylates. Examples of dicarboxylic acids suitable for thepolymerization to form polyarylates have the structure of Formula(XVII):

in which, for the aliphatic polyarylates. R¹⁴ is selected from saturatedand unsaturated, substituted and unsubstituted alkyl or alkylaryl groupscontaining up to 18 carbon atoms, and preferably from 2 to 12 carbonatoms. For the aromatic polyarylates, R¹⁴is selected from aryl groupscontaining up to 18 carbon atoms and preferably from 6 to 12 carbonatoms. In sonic embodiments, R¹⁴ is defined as above for R⁸.

R¹⁴ is preferably selected so that the dicarboxylic acids employed asstarting materials are either important naturally-occurring metabolitesor highly biocompatible compounds. Examples of preferred aliphaticdicarboxylic acid starting materials are described elsewherein herein.

The polyarylates can also be prepared by the method disclosed by Higashiet al., Polym. Sci.: Polym. Chem. Ed., 21, 3233-9 (1983) usingarylsulfonyi chloride as the condensing agent, by the process of Higashiet al., J. Polym. Sal Polypi. Chem. Ed., 21, 3241-7 (1983) usingdiphenyl chlorophosphate as the condensing agent., by the process ofFligashi et al., S. Potym, Polym, Chem. Ed., 24, 97-102 (1986) usingthionyl chloride with pyridine as the condensing agent, or by theprocess of Elias, et al., Maltromol. Chem., 182, 681-6 (1981) usingthionyl chloride with triethylamine. A preferred polyesterilicationprocedure is the method disclosed by Moore et al., Macromol., 23, 65-70(1990) utilizing carbodiimide coupling reagents as the condensing agentswith the specially designed catalyst DPTS.

A particularly preferred polyesterification technique modifies themethod of Moore to utilize art excess of the carbodiimide couplingreagent. This technique tends to produce aliphatic polyarylates havingmolecular weights greater than those obtained by Moore. Essentially anycarbodiimide commonly used as a coupling reagent in peptide chemistrycan be used as a condensing agent in the preferred polyesterificationprocess. Such carbodiimides are well-known and disclosed in Bodanszky,Practice of Peptide Synthesis (Springer-Verlag, New York, 1984) andinclude dicyclohexylcarbodimide, diisopropylcarbodiimide,1-(3-dimethylamino-propyl)-3-ethyl carbodiimide hydrochloride,N-cyclohexyl-N′-(2′-morpholinoethyl)-carbodiimide-metho-p-toluenesulfonate, N-benzyl-N′-3′-dimethyl-aminopropyl-carbodiimidehydrochloride, 1-ethyl-3-(3-dimethylaminopropyl)-carbodiimidemethiodide, N-ethylcatbodiimide hydrochloride, and the like. Thepreferred carbothimides are dicyclohexyl carbodiimide anddiisopropylcarbodimide.

An esterification reaction mixture can generally be formed by contactingexactly equimolar quantities of the hydroxyacid-phenolic compound andthe dicarboxylic acid in a solvent. Suitable solvents include methylenechloride, tetrahydrofinan. dimethylformamide, chloroform, carbontetrachloride and N-methyl pyrrolidinone. It is not necessary to bringall reagents into complete solution prior to initiating the pol_(i)reaction, although the polymerization of slightly soluble monomers suchas desainlitotyrosyltyTOSine ethyl ester and succinic acid willtypically yield higher molecular weight polymers when the amount ofsolvent is increased. The reaction mixture can also be heated gently toaid in the partial dissolution of the reactants.

The polyarylates can be worked up and isolated by known methods commonlyemployed in the field of synthetic polymers to produce as variety ofuseful articles with valuable physical and chemical properties, allderived from tissue compatible monomers. The useful articles can beshaped by conventional polymer-forming techniques such as extrusion,compression molding, injection molding, and the like. molded articlesprepared from the polyarylates are useful, inter alia, as degradablebiomaterials for medical implant applications. Such applications includethe use of the molded articles as vascular grafts and stems, boneplates, sutures, implantable sensors, barriers for surgical adhesionprevention, implantable drug delivery devices and other therapeutic aidsand articles which decompose harmlessly within a known period of time.

In some embodiments the polymers described herein contain phosphorus.The versatility of these polymers may come from the versatility of thephosphorus atom, which is known for a multiplicity of reactions. Itsbonding may involve the 3p orbitals or various 3s-3p hybrids; spdhybrids are also possible because of the accessible of orbitals. Thus.the physico-chemical properties of the poly(phosphoesters) may bereadily changed by varying either the R or R′ group. Thebiodegradability of the polymer is due primarily to the physiologicallylabile phosphoester bond in the backbone of the polymer, By manipulatingthe backbone or the sidechain, a wide range of biodegradation rates areattainable.

As those skilled in the art would appreciate, when a monomer has anunsymmetrical structure having two equally or similarly reactivefunctional groups fir polymerization, the polymers formed would largelycontain the monomeric units in random orders.

Poly(phosphonates) may be prepared by a similar condensation betweenappropriately substituted dichlorides and diols.

Poly(phosphites) may be prepared from glycols in a two-step condensationreaction. A 20% molar excess of a dimethylphosphite is preferably usedto react with the glycol, followed by the removal of themethoxyphosphonyl end groups in the oligomers by high temperature. Anadvantage of melt polycondensation is that it avoids the use of solventsand large amounts of other additives, thus making purification morestraightforward it may also provide polymers of reasonably highmolecular weight. Polymerization may also be carried out in solution. Achlorinated organic solvent may be used, such as chloroform,dichloromethane, or dichloroethane. To achieve high molecular weights,the solution polymerization is preferably run in the presence ofequimolar amounts of the reactants and, more preferably, astoichiometric amount of an acid acceptor or a Lewis acid-type catalyst.Useful acid acceptors include tertiary amines such as pyridine ortriethylamine. Examples of useful Lewis acid-type catalysts includemagnesium chloride and calcium chloride. The product may be isolatedfrom the solution by precipitation in a non-solvent and purified toremove the hydrochloride salt by conventional techniques known to thoseof ordinary skill in the art, such as by washing with an aqueous acidicsolution, e.g., dilute HCl.

Halogenated phenolic monomers may also be polymerized to formpolyiminocarbonates utilizing cyanogen bromide. Polyiminocarbonates arestructurally related to polycarbonates. The polyiminocarbonates haveimino groups in the places typically occupied by carbonyl oxygen in thepolycarbonates. Thus, the polyiminocarbonates have linkages according tothe formula:

Inclusion of iminocarbonate linkages may impart a significant degree ofhydrolytic instability to the polymer. The polyiminocarbonates havedesirable mechanical properties akin to those of the correspondingpolycarbonates.

Starting materials described herein are available commercially, areknown, or may be prepared by methods known in the art. Additionally,starting materials not described herein are available commercially, areknown, or may be prepared by methods known in the art.

Starting materials may have the appropriate substituents to ultimatelygive desired products with the corresponding substituents.Alternatively, substiuents may be added at any point of synthesis toultimately give desired products with the corresponding substituents.

The synthetic schemes illustrated herein show methods that may be usedto prepare the compounds of preferred embodiments. One skilled in theart will appreciate that a number of different synthetic reactionschemes may be used to synthesize the compounds of preferred.embodiments. Further, one skilled in the art will understand that anumber of different solvents, coupling agents and reaction conditionsmay be used in the synthetic reactions to yield comparable results.

One skilled in the art will appreciate variations in the sequence and,further, will recognize variations in the appropriate reactionconditions from the analogous reactions shown or otherwise known whichmay be appropriately used in the processes above to make the compoundsof preferred embodiments.

In the processes described herein for the preparation of the compoundsof preferred embodiments, the requirements for protective groups aregenerally well recognized by one skilled in the art of organicchemistry, and accordingly the use of appropriate protecting groups isnecessarily implied by the processes of the schemes herein, althoughsuch groups may not be expressly illustrated. Introduction and removalof such suitable protecting groups are well known in the art of organicchemistry; see for example, T. W. Greene, “Protective Groups in OrganicSynthesis”. Wiley (New York), 1999,

The products of the reactions described herein can be isolated byconventional means such as precipitation, extraction, distillation,chromatography, and the like.

The salts of the compounds described herein can be prepared by reactingthe base or acid as appropriate with a stoichiometric equivalent, of thecompound.

In some embodiments, the polymer comprises poly(ether carbonate) with atyrosol-bioactive moiety. A hydroxyacid-tyrosol compound can be combinedwith the

PEG in methylene chloride and phosgene can be added as a solution intoluene. The reaction would be completed in around 9 minutes. In someembodiments, this reaction is carried out for from 1-60 minutes. In anembodiment, the polymer comprises poly(hydroxyacid-tyrosol carbonate)pendant bioactive moiety groups.

In another aspect the present invention provides a medical device thatcomprises a polymer and/or polymer composition as described herein. Forexample, an embodiment provides a stent that comprises a polymercomposition as described herein. Another embodiment provides a method oftreating a body lumen, comprising deploying the stem within the bodylumen. These and other embodiments are described in greater detailbelow.

Definitions

The term “biodegradable,” as used herein, refers to a property ofpolymer whose molecular weight goes down because of hydrolysis orenzymatic reactions under physiological conditions such that the polymeris transformed into lower molecular weight oligomers in a period not toexceed four (4) years.

The term “oligomer,” as used herein, refers to a hydrolyzed product of apolymer, whose molecular weight is less than 10% of the originalpolymer.

The terms “alkyl”, “alkylene” and similar terms have the usual meaningknown to those skilled in the art and thus may be used to refer tostraight or branched hydrocarbon chain fully saturated (no double ortriple bonds) hydrocarbon group. Terminal alkyl groups, e.g., of thegeneral formula —C_(n)H_(2n+1), may be referred to herein as “alkyl”groups, whereas linking alkyl groups, e.g., of the general formula—(CH₂)_(n)—, may be referred to herein as “alkylene” groups. The alkylgroup may have 1 to 50 carbon atoms (whenever it appears herein, anumerical range such as “1 to 50” refers to each integer in the givenrange, e.g., “1 to 50 carbon atoms” means that the alkyl group mayconsist of 1 carbon atom, 2 carbon atoms, 3 carbon atoms, e.g., up toand including 50 carbon atoms, although the present definition alsocovers the occurrence of the term “alkyl” where no numerical range isdesignated). The alkyl group may also be a medium site alkyl having 1 to30 carbon atoms. The alkyl group could also be a “lower alkyl”, which isdefined as having 1 to 6 carbon atoms. The alkyl group of the compoundsmay be designated as “C₁-C₄ alkyl” or similar designations. By way ofexample only, “C₁-C₄ alkyl” indicates that there are one to four carbonatoms in the alkyl chain, i.e., the alkyl chain is selected from thegroup consisting of methyl, ethyl, propyl, iso-propyl, n-butyl,iso-butyl sec-butyl, and t-butyl. Typical alkyl groups include, but arein no way limited to, methyl, ethyl, propyl, isopropyl, butyl, isobutyl,tertiary butyl, pentyl, hexyl and the like.

The alkyl group may be substituted or unsubstituted. When substituted,the substituent group(s) is(are) one or more group(s) individually andindependently selected from alkenyl alkynyl, cycloalkyl, cycloalkenyl,cycloalkynyl, atyl, heteroaryl, heteroalicyclyl aralkyl, heteroaralkyl,(heteroalicyclypalkyl, hydroxy, protected hydroxyl, alkoxy, aryloxy,acyl, ester, mercapto, alkylthio arylthio, cyano, halogen, carbonyl,thiocarbonyl, O-carbamyl, N-carbamyl, O-thiocathamyl, N-thiocarbamyl,C-amido, N-amido, S-sulfonamido, N-sulfonamido, C-carboxy, protectedC-carboxy, O-carboxy, isocyanato, thiocyanato, isothiocvanato, nitro,sibyl, sulfenyl, sulfinyl, sulfonyl, haloalkyl, haloalkoxy,trihalomethanesulfonyl, trihalomethanesulfonamido, and amino, includingmono- and di-substituted amino groups, and the protected derivativesthereof Wherever a substituent is described as being “optionallysubstituted” that substituent may be substituted with one of the abovesubstituents.

An “alkylaryl” is an aryl group connected, as a substituent, via analkylene group. The alkylene and aryl group of an aralkyl may besubstituted or unsubstituted. Examples include but are not limited tobenzyl, substituted benzyl, 2-phenylethyl 3-phenylpropyl, andnaphtylalkyl. In some cases, the alkylene group is a lower alkylenegroup containing 1 to 6 carbon atoms. An aikylaryl group may besubstituted or unstubstituted.

As noted above, alkyl groups may link together other groups, and in thatcontext may be referred to as alkylene groups. Alkylene groups are thusb.iradical tethering groups, forming bonds to connect molecularfragments via their terminal carbon atoms. Examples include but are notlimited to methylene (—CH₂—), ethylene (—CH₂CH₂—), propylene(—CH₂CH₂CH₂—), and butylene (—(CH₂)₄—) groups. An alkylene group may besubstituted or unsubstituted.

The terms “alkenyl”, “alkenylene” and similar terms have the usualmeaning known to those skilled in the art and thus may be used to referto an alkyl or alkylene group that contains in the straight or branchedhydrocarbon chain containing one or more double bonds, An alkenyl groupmay be unsubstituted or substituted. When substituted, thesubstituent(s) may be selected from the same groups disclosed above withregard to alkyl group substitution unless otherwise indicated.

An “amide” is a chemical moiety with formula —(R)_(n)—C(═O)NHR′ or—(R)_(n)—NHC(═O)R′, where R and R′ are independently selected from thegroup consisting of cycloalkyl, aryl, heteroaryl (bonded through a ringcarbon) and heteroalicyclic (bonded through a ring carbon), and where nis 0 or 1. An amide may be an amino acid. or a peptide molecule attachedto a molecule of the present invention, thereby forming a prodrug. An“amide linkage” is an amide group (—C(═O)NH—) that links two chemicalmoieties to one another.

Any amine, hydroxy, or carboxyl side chain on the compounds disclosedherein can be esterified or amidified. The procedures and specificgroups to be used to achieve this end are known to those of skill in theart and can readily be found in reference sources such as Greene andWins, Protective Groups in Organic Synthesis, 3rd Ed., John Wiley &Sons. New York, N.Y., 1999, which is incorporated by reference herein inits entirety.

As used herein, “aryl” refers to a carbocyclic (all carbon) ring or twoor more fused rings (rings that share two adjacent carbon atoms) thathave a .fully delocalized pi-electron system. Examples of aryl groupsinclude, but are not limited to, benzene, naphthalene and azulene. Anaryl group may be substituted or unsubstituted. When substituted,hydrogen atoms are replaced by substituent group(s) that is(are) one ormore groupts) independently selected from alkenyl, alkynyl, cycloalkyl,cyclo-alkenyl, cycloalkynyl, aryl, heteroaryl, heteroalicyclyl, aralkyl,heteroaralkyl, (hetero-alicyclylialkyl, hydroxy, protected hydroxyl,alkoxy, inyloxy, acyl, ester, mercapto, alkylthio, arylthio, cyano,halogen, carbonyl, thiocarbonyl, O-carbamyl, N-carbamyl, O-thiocarbamyl,N-thiocarbamyl, C-amido, N-amido, S-sulfonamido, N-sulforumido,C-carboxy, protected C-carboxy, O-carboxy, isocyanato, thiocyanato,isothiocyanato, nitro, silyl, sulfenayl, sulfinyl, sulfonyl, haloalkyl,haloalkoxy, trihalomethanesulfonyl, trihalomethanesulfonamido, andamino, including mono- and di-substituted amino groups, and theprotected derivatives thereof. When substituted, substituents on an arylgroup may form a non-aromatic ring fused to the aryl group, including acyclo-alkyl, cycloalkenyl, cycloalkynyl, and heterocyclyl.

As used herein, “heteroalkyl” refers to an alkyl group where one or morecarbon atoms has been replaced with a heteroatom, that is, an elementother than carbon, including but not. limited to, nitrogen, oxygen andsulfur.

The terms “heteroalkyl”, “heteroalkylene,” and similar terms have theusual meaning known to those skilled in the art and thus may be used torefer to an alkyl group or alkylene group as described herein in whichone or more of the carbons atoms in the backbone of alkyl group oralkylene group has been replaced by a heteroatom such as nitrogen,sulfur and/or oxygen, Likewise, the term. “hetero-alkenylene” may beused to refer to an alkenyl or alkenylene group in which one or more ofthe carbons atoms in the backbone of alkyl group or alkylene group hasbeen replaced by a heteroatom such as nitrogen, sulfur andlor oxygen.

As used herein, “heteroarl” refers to an aryl group where one or morecarbon atoms has been replaced, with a heteroatom, that is, an elementother than carbon, including but not limited to, nitrogen, oxygen andsulfur.

For convenience and conciseness, sometimes the terms “alkyl”, “alkenyl”,“alkynyl”, “aryl”, “heteroaryl”, and “alkylaryl”, or the like, may beused to refer to the corresponding linking groups when they serve toconnect two moieties of a molecule, either monomeric or polymeric, whichshould be readily understood by those skilled in the art, That is, onsuch occasions. “alkyl” should be interpreted as “alkylene”; “alkenyl”should be interpreted as “alkenylene”, “aryl” should be interpreted as“arylene”; and so on,

A “heavy atom” is an atom that., when attached to a polymer, renders thepolymer easier to detect by an imaging technique as compared to apolymer that does not contain the heavy atom. Since many polymerscontain relatively low atomic number atoms such as hydrogen, carbon,nitrogen. oxygen, silicon and sulfur, in most cases heavy atoms have anatomic number of 17 or greater. Preferred heavy atoms have an atomicnumber of 35 or greater, and include bromine, iodine, bismuth, gold,platinum tantalum, tungsten, and barium.

A “hydrocarbon” is an organic compound consisting entirely of hydrogenand. carbon. Examples of hydrocarbons include unsubstituted alkylgroups, unsubstituted aryl groups, and unsubstituted alky lacy! groups.Any substitution to an alkyl group, aryl group, or alkylatyl group in ahydrocarbon would only comprise carbon and/or hydrogen atoms.

As used herein, the terms “macromer”, “macromeric” and similar termshave the usual meaning known to those skilled in the art and thus may beused to refer to oligomeric. and polymeric materials that arefunctionalized with end groups that are selected so that the macromerscan he copolymerized with other macromers or monomers. A wide variety ofmacromers and methods for making them are known to those skilled in theart. Examples of suitable macromers include hydroxy endcapped polylacticacid macromers, hydroxy endcapped polyglycolic acid macromers, hydroxyendcapped poly acid,co-glycolic acid) macromers, hydroxy endcappedpolycaprolactone macromers, poly diol) macromers, hydroxy end-cappedpoly(alkylene oxide) macromers and hydroxy endcapped polydioxanonemacromers.

As used herein, the terms “polymer”, “polymeric” and similar terms havethe usual. meaning known to those skilled in the art and thus may beused to refer to homopolymers, copolymers (e.g., random copolymer,alternating copolymer, block copolymer, graft copolymer) and mixturesthereof, The repeating structural units of polymers may also be referredto herein as recurring units.

As used herein, the term “molecular weight” has the usual meaning knownto those skilled in the art and thus reference herein to a polymerhaving a particular molecular weight will he understood as a referenceto a polymer molecular weight in units of Daltons. Various techniquesknown to those skilled in the art, such as end group analysis (e.g., byNMR) and high pressure size exclusion chromatography (HPSEC, also knownas gel permeation chromatography, “GPC”), may be used to determinepolymer molecular weights. in some cases the molecular weights ofpolymers are further described herein using the terms “number average”molecular weight (Mn) andlor “weight average” molecular weight, (Mw),both of which terms are likewise expressed in units of Daltons and havethe usual meaning known to those skilled in the art.

Unless otherwise indicated, when a substituent is deemed to be“optionally substituted,” it is meant that the substitutent is a groupthat may be substituted with one or more group(s) individually andindependently selected from alkyl, alkenyl, cycloalkyl, aryl,heteroaryl, heteroalicyclic, hydroxyl, alkoxy aryloxy, mercapto,alkylthio, arylthio, cyano halo, carbonyl, thiocarbonyl, O-carbamyl,N-carbarnyl, O-thiocarbamyl, N-thiocarbamyl, C-amido, N-amido,S-sulfortamido, N-sulfonamido, C-carboxy, O-carboxy, isocyanato,thiocyanato, isothiocyanato, nitro, silyl, trihalomethanesulfortyl andamino, including mono- and di-substituted amino groups, and theprotected derivatives thereof. The protecting groups that may form theprotective derivatives of the above substituents are known to those ofskill in the art and may be found in references such as Greene and Wuts,above.

The terms “radiopaque”, “radio-opaque”, “radiopacity”, “radio-opacity”,“radiopacifying” and similar terms have the usual meaning known to thoseskilled in the art and thus may be used to refer to polymer compositionsthat have been rendered. easier to detect using medical imagingtechniques (e.g., by X-ray and/or during fluoroscopy) being theincorporation of heavy atoms into the polymer composition. Suchincorporation may be by mixing, e.g., by mixing an effective amount of aradiopacifying additive such as barium salt or complex, andlor byattachment of effective amounts of heavy atoms to one or more of thepolymers in the polymer composition.

In certain configurations, polymer compositions may he inherentlyradiopa.que. The term “inherently radiopaque” is used herein to refer toa polymer to which a sufficient number of heavy atoms are attached bycovalent or ionic bonds to render the polymer radiopaque. This meaningis consistent with the understanding of those skilled in the art, see,e.g., U.S. Patent Publication No. 2006/0024266, which is herebyincorporated by reference for all purposes, including for the particularpurpose of describing radiopaque polymeric materials.

Whenever a group is described as being “optionally substituted” thatgroup may he unsubstituted or substituted with one or more of theindicated substituents. Likewise, when a group is described as being“unsubstituted or substituted” if substituted, the substituent may beselected from one or more the indicated substituents.

Unless otherwise indicated, when a substituent is deemed to be“optionally substituted,” or “substituted” it is meant that thesubstituent is a group that may be substituted with one or more group(s)individually and independently selected from alkyl, alkenyl, alkynyl,cycloalkyl, cycloalkertyl, cycloalkynyl, aryl, heteroaryl,heteroalicyelyt, aralkyl, heteroaralkyl, (heteroalicyclyl)alkyl,hydroxy, protected hydroxy, alkoxy, aryloxy, acyl, ester, mercapto,cyano, halogen. carbonyl, thiocarbonyl, O-carbamyl. N-carbamyl,O-thiocarbamyl, N-thiocarbamyl, C-amido, N-amido, S-sulfonamido,N-sultbnamido, C-carboxy, protected C-carboxy, O-carboxy, isocyanato,thiocyanato, isothiocyanato, nitro, silyl, sulfenyl, sulfinyi, sulfonyl,haloalkyl, ha oal kox y trihaloniethanesulfonyt. triha lom ethanesufonarn ido, and amino, including mono- and di-substituted amino groups,and the protected derivatives thereof. Similarly, the term “optionallyring-halogenated” may be used to refer to a group that optionallycontains one or more (e.g., one, two, three or four) halogensubstituents on the aryl and/or heteroaryl ring. The protecting groupsthat may form the protective derivatives of the above substituents areknown to those of skill in the art and may he found in references suchas Greene and Wuts, Protective Groups in Organic Synthesis, 3^(rd) Ed.,John Wiley & Sons, New York, N.Y., 1999, which is hereby incorporated byreference in its entirety.

It is understood that, in any compound. described herein having one ormore chiral centers, if an absolute stereochemistry is not expresslyindicated, then each center may independently be of R-configuration orS-configuration or a mixture thereof. Thus, the compounds providedherein may be enantiomerically pure or he stereoisomeric mixtures. Thus,the aipha-hydroxyacids employed as subunits in the monomers and theirresulting polymers can be chiral, vide infra. For example, thelactate-derived monomers and polymers can be derived from L-lactic acid,D-lactic acid or the racemic D,L-lactic acid. Further, specific blocksof L-lactate, .D-lactate and/or D,L-lactate can be incorporated in anyorder. In addition it is understood that, in any compound having one ormore double bond(s) generating geometrical isomers that can be definedas E or Z each double bond may independently be F or Z a mixturethereof. Likewise, all tautomeric forms are also intended to beincluded.

The following abbreviations are used to identify various iodinatedcompounds. TE stands for tyrosine ethyl ester, DAT stands fordesaminotyrosine and DTE for desaminotyrosyl tyrosine ethyl ester. PTEstands for hydroxy-phenoxy-l-oxoethyl tyrosine ethyl ester. Ty standsfor tyrosol. The polymer obtained by phosnenation of DTE is denoted aspoly(DTE carbonate). An “I” before the abbreviation showsmono-iodination (e.g. ITE stands for mono-iodinated TE) and an I₂ beforethe abbreviation shows di-iodination (e.g. I₂DAT stands for di-iodinatedDAT). In DTE, if the “I” is before D, it means the iodine is on DAT andif “I” is after D. it means the iodine is on the tyrosine ring (e.g.DI₂TE stands for DTE with 2 iodine atoms on the tyrosine ring). Thefollowing diagram illustrates this nomenclature further.

General Structure of Iodinated DIE Monomer

IDTE: X^(1a)═I, X^(1b)═H, X^(2a)═H. X^(2b)═H.

I₂DTE: X^(1a)═I, X^(1b)═I, X^(2a)═H, X^(2b)═H

DI₂TE: X^(1a)═X, X^(1b)═H, X^(2a)═I. X^(2b)═I

IDITE: X^(1a)═I, X^(1b)═Hm X^(2a)═I, X^(2b)═H

For PTE, PTH, IPTE, I₂PTE, PI₂TE, etc., the DAT CH₂CH₂ is replaced withOCH₂.

As used herein, the abbreviations for any protective groups, ammo acidsand other compounds are, unless indicated otherwise, in accord withtheir common usage, recognized abbreviations, or the ILIPAC-IUPCommission on Biochemical Nomenclature (See, Biochem. 11:942-944(1972)).

The term “halogen atom,” as used herein, means any one of theradio-stable atoms of column 7 of the Periodic Table of the Elements,e.g., fluorine, chlorine, bromine, or iodine, with bromine and iodinebeing preferred.

The term “ester” refers to a chemical moiety with formula—(R)_(n)—COOR′, where R and R′ are independently selected from the groupconsisting of alkyl, cycloalkyl, aryl, heteroaryl (bonded through a ringcarbon) and heteroalicyclic (bonded through a ring carbon), and where nis 0 or I. An “ester linkage” is an ester group that links two chemicalmoieties to one another.

The terms “purified,” “substantially purified,” and “isolated” as usedherein refer to compounds disclosed herein being substantially free ofother, dissimilar compounds with which the compounds of the inventionare normally associated in their natural state, so that the compounds ofthe invention comprise at least 0.5%, 1%, 5%, 10%, or 20%, and mostpreferably at least 50% or 75% of the mass, by weight, of a givensample.

It is understood that the polymers described herein may he used inaccordance with preferred aspects of the invention as a homogeneouspolymer, as a copolymer, andlor as a polymer blend.

Although the inventors do not wish to be bound by or to any particulartheory of operation, the inventors believe that the beneficialcombination of properties associated with the medical devices of thepresent invention are attributable, at least in part, to certaincharacteristics of the polymers disclosed herein, from which the devicesare made.

The tyrosol-lactate diol macromers, as described below, have the uniqueattribute of possessing the crystallizable poly-lactate units on onlyone side of the macromer. This derives from the surprising observationthat when ring opening of a lactide (or lactone or cyclic carbonate) isinitiated, with tyrosol, only the aliphatic OH group participates in thering opening reactions, thereby leaving the phenolic OH free, Oneembodiment has the following structure:

For a conventional diol macromer prepared from a lactide and ana_(j)o-diol, the initiating dint reacts with the lactide equally on bothends of the diol. One embodiment using propane diol has the followingstructure:

In this standard diol case, the diol initiator is generally embedded inthe center of the resulting macromer entity and acts as a significantdisruptor to molecular chain alignment. As a consequence, the polymerderived from these macron units will have a lower melt transition, heatof fusion, and glass transition temperature than would be expected fromnon-disrupted polylactate chain segments.

Conversely, the tyrosol-polylactate units have no disruptor in themiddle of the extended chain segments. This has the unexpected influenceof providing a final polymer with a higher wet and dry glass transitiontemperature (Tg) and a crystalline phase with higher melt temperatureand heat of fusion, thus a better crystalline phase. The higher wet Tgof biodegradable structural polymers is critically significant in thatthe wet Ig needs to be sufficiently above body temperature to maintainthe required level of mechanical structural support. Because of theirunique chain architecture, the tyrosol-polylactates provide a higher wetTg. Obtaining the correct wet Tg and crystalline phase is not possibleusing the standard diol chemistry

The bioresorbable, inherently radiopaque stems disclosed in accordancewith preferred embodiments of the present invention may be used, forexample, to temporarily treat a blood vessel as in traditionalapplications which generally include delivery through a catheter.

In some embodiments polymers prepared from sufficient amounts of themonomeric starting materials described herein and having at least onebromine- or iodine-substituted aromatic ring are radio-opaque, such asthe polymers prepared from radiopaque diphenol compounds preparedaccording to the disclosure of U.S. Pat. No. 6,475,477, as well as hedisclosure of U.S. Pat. No. 7,649,150, the disclosures of both of whichare incorporated, herein by reference. The iodinated and brominatedhydroxyacid-phenolic monomers of the present invention can also beemployed as radio-opacifying biocompatible non-toxic additives for otherpolymeric biomaterials. Bromine and iodine substituted aromatic monomersof the present invention can be prepared by well-known iodination andbromination techniques that can be readily employed by those of ordinaryskill in the art in view of the guidance provided herein without undueexperimentation. In some embodiments, the halogenated aromatic compoundsfrom which the halogenated aromatic monomers of the present inventionare prepared typically undergo ortho-directed halogenation. The term,‘ortho-directed’, is used herein to designate orientation of the halogenatom(s) relative to the phenoxy alcohol group.

Benzyl ester-containing homopolymers and copolymers may be converted tocorresponding free carboxylic acid homopolymers and copolymers throughthe selective removal of the benzyl groups by the palladium catalyzedhydrogenolysis method disclosed by co-pending and commonly owned U.S.Pat. No. 6,120,491, the disclosure of which is incorporated herein byreference.

Tert-butyl ester-containing homopolymers and copolymers may be convertedto corresponding free carboxylic acid homopolymers and copolymersthrough the selective removal of the tert-butyl groups by the acidolyismethod disclosed by the above-referenced U.S. Pat. No. 7,649,150, alsoincorporated herein by reference.

After polymerization, appropriate work up of the polymers in accordancewith preferred embodiments of the present invention may be achieved byany of a variety of known methods commonly employed in the field ofsynthetic polymers to produce a variety of useful articles with valuablephysical and chemical properties, all derived from tissue compatiblemonomers. The useful articles can be shaped by conventionalpolymer-forming techniques such as extrusion, compression molding,injection molding, solvent casting, spin casting, wet spinning,combinations of two or more thereof, and the like. Shaped articlesprepared from the polymers are useful, inter alia, as degradablebiomaterials for medical implant applications. Such applications includethe use of shaped articles as vascular grafts and stents.

Polymers according to the present invention also include polyethers,polyurethanes, poly(carbamates), poly(thiocatbonates),poly(carbonodithionates) and poly(thiocarbamates), which may be preparedfrom the hydroxyacid, phenolic compounds of the present invention inaccordance with known methods.

Random or block copolymers of the polymers of the present invention witha poly(alkylene oxide) may be prepared according to the method disclosedin U.S. Pat. No. 5,658,995, the disclosure of which is also incorporatedby reference. The poly(alkylene oxide) is preferably a polyethyleneglycol) block/unit typically having a molecular weight of less thanabout 10,000 per win. More typically, the poly(ethylene glycol)block/unit has a molecular weight less than about 4000 per unit. Themolecular weight is preferably between about 1000 and about 2000 perunit.

The molar fraction of poly(ethylene glycol) units in block copolymersmay range from greater than zero to less than 1, and is typicallygreater than zero up to about 0.5, inclusive. More preferably the molarfraction is less than about 0.25 and yet more preferably, less thanabout 0.1. in a more preferred variations, the molar fraction may varyfrom greater than about 0.001 to about 0.08, and most preferably,between about 0.025 and about 0.035.

Unless otherwise indicated, the molar fractions reported herein arebased on the total molar amount of poly(alkylene glycol) and non-glycolunits in the polymers

After polymerization, appropriate work up of the polymers in accordancewith preferred embodiments of the present invention may be achieved byany of a variety of known methods commonly employed in the field ofsynthetic polymers to produce a variety of useful articles with valuablephysical and chemical properties, all derived from tissue compatiblemonomers. The useful articles can be shaped by conventional polymerthermo-forming techniques such as extrusion and injection molding whenthe degradation temperature of the polymer is above the glass transitionor crystalline melt temperature, or conventional non-thermal techniquescan be used, such as compression molding, injection molding, solventcasting, spin casting, wet spinning. Combinations of two or more methodscan be used. Shaped articles prepared from the polymers are useful,inter alia, as degradable biomaterials for medical implant applications.

Medical Uses

Various embodiments of the polymer compositions described herein,preferably derived from tissue compatible monomers, may be used toproduce a variety of useful articles with valuable physical and chemicalproperties. The useful articles can be shaped by conventional polymerthermoing techniques such as extrusion and injection molding when thedegradation temperature of the polymer is above the glass transition orcrystalline melt temperature(s), or conventional non-thermal techniquescan be used, such as compression molding, injection molding, solventcasting, spin casting, wet spinning. Combinations of two or more methodscan be used. Shaped articles prepared from the polymers are useful,inter alia, as biocompatible, biodegradable and/or bioresorbablebiomaterials Err medical implant applications.

In one embodiment, the medical device is a stern. It is contemplatedthat a stent may comprise many different, types of forms For instance,the stent may be an expandable stem. In another embodiment, the stentmay be configured to have the form of a sheet stent, a braided stem, aself-expanding stent, a woven stent, a deformable stem, or aslide-and-lock stem. Stent fabrication processes may farther includetwo-dimensional methods of fabrication such as cutting extruded sheetsof polymer, via laser cutting, etching, mechanical cutting, or othermethods, and assembling the resulting; cut portions into stems, orsimilar methods of three-dimensional fabrication of devices from solidforms.

In certain other embodiments, the polymers are formed into coatings onthe surface of an implantable device, particularly a stem, made eitherof a polymer as described herein or another material, such as metal.Such coatings may be formed on stents via techniques such as dipping,spray coating, combinations thereof, and the like. Farther, stents maybe comprised of at least one fiber material, curable material, laminatedmaterial andlor woven material. The medical device may also be a stentgraft or a device used in embolotherapy.

The highly beneficial combination of properties associated withpreferred embodiments of the polymers described herein means thesepolymers are well-suited for use in producing a variety of resorbablemedical devices besides stems, especially implantable medical devicesthat are preferably radiopaque, biocompatible, and have various times ofbioresorption. For example the polymers are suitable for use inresorbable implantable devices with and without therapeutic agents,device components and/or coatings with and without therapeutic agentsfor use in other medical systems, for instance, the musculoskeletal ororthopedic system (e.g., tendons, ligaments, bone, cartilage skeletal,smooth muscles); the nervous system (e.g., spinal cord, brain, eyes,inner ear); the respiratory system (e.g., nasal cavity and sinuses,trachea, larynx, lungs); the reproductive system (e.g., male or femalereproductive); the urinary system (e.g., kidneys, bladder, urethra,ureter); the digestive system (e.g., oral cavity, teeth, salivaryglands, pharynx, esophagus, stomach, small intestine, colon), exocrinefunctions (biliary tract, gall bladder, liver, appendix, recto-analcanal); the endocrine system (e.g., pancreas/islets, pituitary,parathyroid, thyroid, adrenal and pineal body), the heinatopoieticsystem (e.g., blood and bone marrow, lymph nodes, spleen, thymus,lymphatic vessels); and, the integumentary system (e.g., skin, hair,nails, sweat glands, sebaceous glands).

The polymers described herein can thus be used to fabricate woundClosure devices, hernia repair meshes, gastric lap bands drug deliveryimplants, envelopes for the implantation of cardiac devices, devices forother cardiovascular applications, non-cardiovascular stents such asbiliary stems, esophageal steins, vaginal stents, lung-trachea/bronchusstems, and the like.

In addition, the resorbable polymers are suitable for use in producingimplantable, radiopaque discs, plugs, and other devices used to trackregions of tissue removal, for example, in the removal of canceroustissue and organ removal, as well as, staples and clips suitable for usein wound closure, attaching tissue to bone and/or cartilage, stoppingbleeding (homeostasis), tubal ligation., surgical adhesion prevention,and the like. Applicants have also recognized that preferred embodimentsof the polymers described herein are well-suited for use in producing avariety of coatings for medical devices, especially implantable medicaldevices.

Further, in some preferred embodiments, the present polymers may beadvantageously used in making various resorbable orthopedic devicesincluding, for example, radiopaque biodegradable screws (interferencescrews), radiopaque biodegradable suture anchors, and the like for usein applications including the correction, prevention, reconstruction,and repair of the anterior cruciate ligament (ACL), the rotatorcuffirotator cup, and other skeletal deformities.

Other devices that: can be advantageously formed from preferredembodiments of the polymers described herein, include devices for use intissue engineering. Examples of suitable resorbable devices includetissue engineering scaffolds and gratis (such as vascular grafts, graftsor implants used in nerve regeneration). The resorbable polymers mayalso be used to form a variety of devices effective for use in closinginternal wounds. For example biodegradable resorbable sutures, clips,staples, barbed or mesh sutures, implantable organ supports, and thelike, for use in various surgery, cosmetic applications, and cardiacwound closures can be formed.

Various devices useful in dental applications may advantageously beformed according to embodiments of the described herein. For exampledevices for guided tissue regeneration, alveolar ridge replacement fordenture wearers, and devices for the regeneration of maxilla-facialbones may benefit from being radiopaque so that the surgeon or dentistcan ascertain the placement and continuous function of such implants bysimple X-ray imaging.

Preferred embodiments of the polymers described herein are also usefulin the production of bioresorbable, inherently radiopaque polymeric;embolotherapy products for the temporary and therapeutic restriction orblocking of blood supply to treat tumors and vascular malformations,e.g., uterine fibroids, tumors (i.e., chemoenibolization), hemorrhage(e.g., during trauma with bleeding) and arteriovenous malformations,fistulas and aneurysms delivered by means of catheter or syringe.Details of embolotherapy products and methods of fabrication in whichthe polymers described herein may be employed are disclosed in U.S.Patent Publication No. 20050106119 A1, the disclosure of which isincorporated by reference, and particularly for the purpose ofdescribing such products and methods. Embolotherapy treatment methodsare by their very nature local rather than systemic and the products arepreferably fabricated horn the radio-opaque polymers described herein,to permit fluoroscopic monitoring of delivery and treatment.

The polymers described herein are further useful in the production of awide variety of therapeutic agent delivery devices. Such devices may beadapted for use with a variety of therapeutics including, for example,pharmaceuticals drugs) andlor biological agents as previously definedand including biomolecules, genetic material, and processed biologicmaterials, and the like. Any number of transport systems capable ofdelivering therapeutics to the body can be made, including devices fortherapeutics delivery in the treatment of cancer, intravascularproblems, dental problems, obesity, infection, and the like.

A medical device that comprises a polymeric material may include one ormore additional components, e.g., a plasticizer, a filler, acrystallization nucleating agent, a preservative, a stabilizer, aphotoactivation agent, etc., depending on the intended application. Forexample, in an embodiment, a medical device comprises an effectiveamount of at least one therapeutic agent and/or a magnetic resonanceenhancing agent. Non-limiting examples of preferred therapeutic agentsinclude a chemotherapeutic agent, a non-steroidal anti-inflammatory, asteroidal anti-inflammatory, and a wound healing agent. Therapeuticagents may be co-administered with the polymeric material, in apreferred embodiment, at least a portion of the therapeutic agent iscontained within the polymeric material. In another embodiment, at leasta portion of the therapeutic agent is contained within a coating on thesurface of the medical device.

Non-limiting examples of preferred cheinothe.rapeutic agents includetaxanes, tax-Mines, taxols, paclitaxel, dioxorubicin, adriamycin andbleomycin. Non-limiting examples of preferred non-steroidalanti-inflammatory compounds include aspirin, dexa-methasone, ibuprofen,naproxen, and Cox-2 inhibitors (e.g., Rofexcoxib, Celecoxib andValdecoxib). ting examples of preferred steroidal anti-inflammatorycompounds include dexamethasone, beclomethasone, hydrocortisone, andprednisone. Mixtures comprising one r more therapeutic agents may beused. Non-limiting examples of preferred magnetic resonance enhancingagents include gadolinium salts such as gadolinium carbonate, gadoliniumoxide, gadolinium chloride, and mixtures thereof.

The amounts of additional components present in the medical device arepreferably selected to be effective fer the intended application. Forexample, a therapeutic agent is preferably present in the medical devicein an amount that is effective to achieve the desired therapeutic effectin the patient to whom the medical device is administered or implanted.Such amounts may be determined by routine experimentation, in certainembodiments, the desired therapeutic effect is a biological response. Inan embodiment, the therapeutic agent in the medical device is selectedto promote at least one biological response, preferably a biologicalresponse selected from the group consisting of thrombosis, cellattachment, cell proliferation, attraction of inflammatory cells,deposition of matrix proteins, inhibition of thrombosis, inhibition ofcell attachment, inhibition of cell proliferation, inhibition ofinflammatory cells, and inhibition of deposition of matrix proteins. Theamount of magnetic resonance enhancing agent in a medical devices ispreferably an amount that is effective to facilitate radiologic imaging,and may be determined by routine experimentation.

The term “pharmaceutical agent”, as used herein, encompasses a substanceintended for mitigation, treatment, or prevention of disease thatstimulates a specific physiologic (metabolic) response. The term“biological agent”, as used herein, encompasses any substance thatpossesses structural and/or functional activity in a biological system,including without limitation, organ, tissue or cell based derivatives,cells, viruses, vectors, nucleic acids (animal, plant, microbial, andviral) that are natural and recombinant and synthetic in origin and ofany sequence and size, antibodies, polynucleotides, oligonucleotides,cDNA's, oncogenes, proteins, peptides, amino acids, lipoproteins,glycoproteins, lipids, carbohydrates, polysaccharides, lipids,liposomes, or other cellular components or organelles tor instancereceptors and ligands. Further the term “biological agent”, as usedherein, includes virus, serum, toxin, antitoxin, vaccine, blood, bloodcomponent. or derivative, allergenic product, or analogous product, orarsphenamine or its derivatives tor any trivalent organic arseniccompound) applicable to the prevention, treatment, or cure of diseasesor injuries of man (per Section 351(n) of the Public Health Service Act(42 U.S.C. 262(a)). Further the term “biological agent” may include 1)“biomolecule”, as used herein, encompassing a biologically activepeptide, protein, carbohydrate. vitamin, lipid, or nucleic acid producedby and purified from naturally occurring or recombinant organisms,antibodies, tissues or cell lines or synthetic analogs of suchmolecules; 2) “genetic material” as used herein, encompassing nucleicacid (either deoxyribonucleic acid (DNA) or ribonucleic acid (RNA),genetic element, gene, factor, allele, operon, structural gene,regulator gene, operator gene, gene complement, genome, genetic code,codon, anticodon, messenger RNA (mRNA), transfer RNA (tRNA), ribosomalextrachromosomal genetic element, plasmagene, plasmid, transposon, genemutation, gene sequence, exon, intron, and, 3) “processed biologics”, asused herein, such as cells, tissues or organs that have undergone.manipulation. The therapeutic agent may also include vitamin or mineralsubstances or other natural elements.

For devices placed in the vascular system, e.g., a stent, the amount ofthe therapeutic agent is preferably sufficient to inhibit restenosis orthrombosis or to affect some other state of the stented tissue, forinstance, heal a vulnerable plaque, and/or prevent rupture or stimulateendothelialization. The agent(s) may be selected from the groupconsisting of antiproliferative agents, anti-inflammatory, anti-matrixmetalloproteinase, and lipid. lowering, cholesterol modifying,anti-thrombotic and antiplatelet agents, in accordance with preferredembodiments of the present invention. In some preferred embodiments ofthe stem., the therapeutic agent is contained within the stent as theagent is blended with the polymer or admixed by other means known tothose skilled in the art, in other preferred embodiments of the stein,the therapeutic agent is delivered from a polymer coating on the stentsurface. In another preferred variation the therapeutic agent isdelivered by means of no polymer coating. In other preferred embodimentsof the stent, the therapeutic agent is delivered from at least oneregion or one surface of the stein. The therapeutic may be chemicallybonded to the polymer or carrier used for delivery of the therapeutic ofat least one portion of the stent andior the therapeutic may bechemically bonded to the polymer that comprises at least one portion ofthe stent body. In one preferred embodiment, more than one therapeuticagent may be delivered.

In certain embodiments, any of the aforementioned devices describedherein. can be adapted for use as a therapeutic delivery device (inaddition to any other functionality thereof). Controlled therapeuticdelivery systems may be prepared, in which a therapeutic agent, such asa biologically or pharmaceutically active and/or passive agent, isphysically embedded or dispersed within a polymeric matrix or physicallyadmixed with a polymer described herein. Controlled therapeutic agentdelivery systems may also be prepared by direct application of thetherapeutic agent to the surface of an implantable medical device suchas a hioresorbable stent device (comprised of at least one of thepolymers described herein) without the use of these polymers as acoating, or by use of other polymers or substances for the coating.

Therapeutic agent delivery compounds may also be formed by physicallyblending the therapeutic agent to be delivered with the polymersdescribed herein using conventional techniques well-known to those ofordinary skill in the art. For this therapeutic agent deliveryembodiment, it is not essential that the polymer have pendent groups forcovalent attachment of the therapeutic agent.

The polymer compositions described herein containing therapeutic agents,regardless of whether they are in the form of polymer conjugates orphysical admixtures of polymer and therapeutic agent, are suitable forapplications where localized delivery is desired, as well as insituations where a systemic delivery is desired. The polymer conjugatesand physical admixtures may be implanted in the body of a patient inneed thereof, by procedures that are essentially conventional andwell-known to those of ordinary skill in the art.

The polyarylates can also he formed into drug delivery implants thatdegrade to release pharmacologically or biologically active agentswithin a predictable controlled release time. Such controlled drugdelivery systems can be prepared by incorporating the active agents intothe polymer chains as pendant side chains or by cross linking thependant side chains to form a polymeric matrix into which the activeagents are physically embedded or dispersed. Controlled drug deliverysystem implants can also be formed by physically admixing thepolyarylates with a biologically or pharmacologically active agent. Theforegoing procedures are essentially conventional and well-known tothose of ordinary skill in the art.

For controlled drug delivery systems in which a biologically orpharmacologically active agent is physically embedded or dispersed intoa polymeric matrix or physically admixed with a polyarylate, suitablebiologically or pharmacologically active agents include in principle anyactive agent that has to be repeatedly administered over prolongedperiods of time.

An advantage of using the radiopaque, bioresorbable polymers describedherein in therapeutic agent delivery applications is the ease ofmonitoring release of a therapeutic agent and the presence of theimplantable therapeutic delivery system. Because the radiopacity of thepolymeric matrix is due to covalemly attached halogen substituents, thelevel of radiopacity is directly related to the residual amount of thedegrading therapeutic agent deliver matrix still present at the implantsite at any given time after implantation. In preferred embodiments therate of therapeutic release from the degrading therapeutic deliverysystem will be correlated with the rate of polymer resorption. in suchpreferred embodiments, the straight-forward, quantitative measurement ofthe residual degree of radio-opacity will provide the attendingphysician with a way to monitor the level of therapeutic release fromthe implanted therapeutic delivery system.

The following non-limiting examples set farth herein below illustratecertain aspects of the invention. All parts and percentages are by molepercent unless otherwise noted and all temperatures are in degreesCelsius unless otherwise indicated. All solvents were HPLC grade and allother reagents were of analytical grade and used as received, unlessotherwise indicated.

EXAMPLES

All the reagents were purchased in pure form and were used as received.Solvents were of “HPLC” or “ACS reagent” grade.

Generally, the hydroxyacid-phenolic monomers were prepared by reactionof tyrosol with the cyclic dimers of alpha-hydroxyacids (e.g. glycolide, lactide, etc.), cyclic carbonates (e.g. trimethylene carbonate) orlactones, The number average molecular mass, M_(n), of the resultingproducts is determined by the ratio of tyrosol to lactide in thereaction, and was confirmed by ¹NMR spectroscopy. Thehydroxyacid-phenolic monomers in the pure form or as appropriatemixtures were polymerized to the corresponding polycarbonates usingtriphosgene. Similarly, polymerization of the hydroxyacid-phenolicmonomers with diacids produced the corresponding polyesters. Theresulting polymers were compression molded into films. The films weretested for mechanical properties and the generally showed high modulus,tensile strength, and elongation at break, Further details are providedbelow.

Example 1 Preparation of Tyrosyl Lactate282 (TyLactate282)

In a 2-L 3 necked flask equipped with a overhead stirrer, a nitrogeninlet adopter and a thermometer were placed 720.65 g (5.00 mol) ofL-lactide, 690.35 g (5.00 mol) of tyrosol and 2.03 g (5.00 mmol) ofSnatioctoate. The flask was maintained under a slight positive pressureof nitrogen and immersed in an oil bath. While stining the contents ofthe flask the temperature of the oil bath was raised to 130° C. andmaintained at that temperature for 3 h. The flask was then cooled toroom temprature and the contents were dissolved in 3 liters ofdichloromethane (DCM). The resulting, solution was added to 6 liters ofheptane with stirring. The supernatant was siphoned out and theprecipiate was stirred with 3 1 L portions of hepane and dried in avacuum oven at 35° C. for 24 h. HPLC showed approximately 6-8% unreactedtyrosol, 35% of tyrosyl lactate, 36% of tyrosyl dilactate and higheroligomers. The results are confirmed by its ¹H NMR spectrum. Usingsimilar procedures Tyrosyl lactate210, Tyrosyl lactate426, Tyrosyllactate1500, Tyrosyl lactate2500, Tyrosyllactate4000, etc. were obtainedby varying the ratio of tyrosol and lactide. As the ratio of lactideincreased, the amount of residual tyrosol decreased and the productbecame more and more viscous. Tyrosyl lactate1500 and higher homologswere observed to be solids.

Example 2 Preparation of Tyrosyl Glycolate254 (TyGlycolate254)

Tyrosyl Glycolate254 was prepared using procedure similar to that usedfor Tyrosyl lactate282 above. In a 1 L 3 necked flask equipped with anoverhead stirrer, a nitrogen inlet adopter and as thermometer wereplaced 174.1 g (1.5 mol) of glycolide. 207.1 g (1.5 mol) of tyrosol and0.6 g (1.5 mmol) of Sn(II)octoate. The flask was maintained under aslight positive pressure of nitrogen and immersed in an oil bath. Whilestirring the contents of the flask the temperature of the oil bath wasraised to 140° C. and maintained at that temperature for 4 h. The flaskwas then cooled to room temprature and the contents were dissolved in800 mL of dichloromethane (DCM). The resulting solution was added to 1.6liters of beptane with stirring. The supernatant was siphoned out andthe precipiate was stirred with 500 mL of hepane 3 times and then driedin a vacuum oven at 35° C. for 24 h. E NMR spectrum showed approximately6% unreacted tyrosol. Using similar procedures Tyrosyl glycolates ofmolecular weight (Mn) 300 to 4000 were prepared.

Example 3 Iodination of Tyrosyl Lactale282

Iodination of Tyrosyl Lactate282 is carried out using known procedures,200 mL of KlCl₂ solution (2M) is added to 56.4 g (0.2 mol) of TyrosylLactate282 in 250 mL of 95% ethanol and stirring the resulting solutionfor 1 h. It is then treated with 400 mL of water and the oil thatseparates is stirred with 100 mL of 2% sodium thiosulfate solution for 2h. The brown solid obtained is dissolved in ethanol and treated withcharcoal and filtered and evaporated to dryness to obtain diiodotyrosyllactate282. The product is characterized by hple and NMR.

Example 4 Preparation of Tyrosyl Trimethylene Carbonate

Tyrosyl trimethylene carbonate is prepared using procedure similar tothat used for Tyrosyl lactate282. above. In a 1 L 3 necked flaskequipped with an overhead stirrer, and a nitrogen inlet adopter and. athermometer were placed 102.09 g (1.0 mol) of, trimethyelene carbonate138.07 g (1.0 mol) of tyrosol and 0.4 g (1.0 mmol) of Sn(II)octoate. Theflask was maintained under a slight positive pressure of nitrogen andimmersed in a oil bath. While stirring the contents of the flask thetemperature of the oil bath was raised to 130° C. and maintained at thattemperature for 3 h. The flask was then cooled to room teniprature andthe contents were dissolved in 500 mL of dichloromethane (DCM). Theresulting solution was added to 1.0 liters of heptane with stirring. Thesupernatant was siphoned out and the precipiate was stirred with 500 mLof hepane 3 times and then dried in a vacuum oven at 35° C. for 24 h. ¹HNMR spectrum showed approximately unreacted tyrosol. Using similarprocedures Tyrosyl trimethylene carbonates of molecular weight (Mn) 300to 4000 were prepared.

Example 5 Preparation of Tyrosyl Caprolactone

Tyrosyl caprolactone us prepared using procedure similar to that usedfor Tyrosyl trimethylene carbonate above. In a 1 L 3 necked flaskequipped with an overhead stirrer, and a nitrogen inlet adopter and athermometer are placed 114.14 g (1,0 mol) of , caprolactone 138.07 g(1.0 mol) of tyrosol and 0.4 g (1.0 mmol) of Sn(II)ocloate. The flask ismaintained under a slight positive pressure of nitrogen and immersed ina oil bath. While stirring the contents of the flask the temperature ofthe oil bath is raised to 130° C. and maintained at that temperature for3 h. The flask is then cooled to room temprature and the contents weredissolved in 500 mL of dichloromethane(DCM). The resulting solution isadded to IA) liters of beptane with stirring. The supernatant issiphoned out and the precipiate is stirred with 500 mL of hepane 3 timesand then dried in a vacuum oven at 35° C. for 24 h. ¹HNMR spectrumshowed approximately 6% unreacted t:srrosol. Using similar proceduresTyrosyl caprolactones of molecular weight (Mn) up to 4000 are prepared,

Example 6 Preparation of Poly(50% PrD-diI₂DAT-co-50% TyLactate426Carbonate)

In a 5 L 4-necked round-bottomed flask equipped with a mechanicalstirrer, a liquid addition device, and nitrogen inlet were placed 150 g(0.17 mol) of PrD-di I₂DAT, 150 g (0.35 mol) of TyLactate426, 155 g(1.96 mol) of pyridine, and 2.1 L of DCM and stirred for 15 min to get aclear solution. Triphosgene (54.3 g, 0.523 mol of phosgene) wasdissolved in 150 mL of DCM and the solution was introduced into thereaction flask over 3 hours, After the addition was complete, the 500mL. of water was added to the reaction mixture and stirred for 5 min.After allowing the layers to separate, the top aqueous layer was removedand discarded. The washing was repeated with two additional 500 mLportions of Dl water. The reaction mixture was then precipitated with300 mL of isopropyl alcohol (IPA). The resulting gel was ground twicewith 200 mL portions of IPA in 1 L laboratory blender. The product wasisolated by vacuum filtration and dried in a vacuum oven at 80° C., Thepolymer had an absolute molecular weight of 221 Kda (PDI−1.86) and glasstransition temperature (Tg) of 72° C. (wet Tg was 50° C. using DMA). ¹HN MR spectrum of the polymer was in agreement with the structure.Compression molding at 190° C. gave a uniform transparent film whichexhibited tensile modulus, tensile stress at yield (σ), and elongationat break respectively of 249 ksi, 7.7 ksi and 333%. Using similarprocedures, copolymers with 40%, and 30% TyLactate426 were also preparedby varying the ratio of PrD-di I₂DAT to TyLactate426. This polymer couldbe injection moldable at 190° C. and melt extrudable with minimaldegradation.

Using similar procedures Poly(50%PrD-diI₂DAT-co-50% TyLactate210carbonate), Poly(50% PrD-diI₂DAT-co-50% TyLactate282 carbonate).Poly(50% PrD-diI₂DAT-co-50% TyLactate1500 carbonate), Poly(50%PrD-diI₂DAT-co-50% Ty Lactate4000 carbonate), and Poly(50%PrD-diI₂-DAT-co-50% TyLactate7000 carbonate) were also prepared.

Example 7 Preparation of Poly(50% PrD-diI₂DAT-co-50%(TyrosyitrimethyleneCarbonate) Carbonate)

Using procedures similar those described in Example 6 substitutingTyrosyl trimethylene carbonate for tyrosyl lactate the title polymersare prepared.

Example 8 Preparation of Py(50%PrDI₂DAT-co-50% TyrosylcaprolactoneCarbonate)

Using procedures similar those described in Example 6 substitutingTyrosyl caprolactone for tyrosyl lactate the titled polymers areprepared.

Example 9 Synthesis of (4-(2-hydroxyethyl)2,6,-diiodophenol)

Iodination of tyrosol was carried out b adding 200 mL of KlCl₂ solution(2M) to 27.6 g (0.2 mol) of tyrosol in 140 mL of 95% ethanol andstirring the resulting solution for 1 h. When treated with 400 mL ofwater, an oil separated which was stirred with 100 mL of 2% sodiumthiosu.lfate solution for 2 h. The brown solid obtained was dissolved inethanol and treated with charcoal and filtered. The pare diiodotyrosol(4-(2-hydroxyethyl)2,6,-dtiodophenol) was obtained in 65% yield and wascharacterized by hplc and NMR.

Example 10 Alternative Preparation of I₂ Tyrosyl Lactate282

The compound of Example 9 is submitted to the reaction conditions ofExample 1 to provide the same product as Example 3.

The foregoing examples and description of the preferred embodimentsshould be taken as illustrating, rather than as limiting the presentinvention as defined by the claims. As will be readily appreciated,numerous variations and combinations of the features set forth above canbe utilized without departing from the present invention as set forth inthe claims. Such variations are not regarded as a departure from thespirit and scope of the invention, and all such variations are intendedto be included within the scope of the following claims.

What is claimed is::
 1. A biocompatible polymer, comprising a recurringunit of formula;

wherein y1 is 0, 1, 2, 3, or 4: X¹ is bromine (Br) or iodine (I); X² andX³ are independently selected from O, S and NR, where .R is H or loweralkyl; R¹ is selected from the group consisting of linear or branchedC₁-C₁₂ alkylene; A is selected from the group consisting of linear orbranched C₁-C₂₄ alkylene, R² is selected, from the group consisting oflinear or branched C₁-C₂₄ alkylene; n1 and n2 are independently numbersfrom 0 to 100, and are average values which can be fractional. where thesum of ni and n2 is at least 1; p is zero or 1; and A¹ is a linkinggroup selected from:

wherein R⁸ is selected from a bond, C₁-C₃₀ alkylene, C₂-C₃₀ alkenylene,C₂-C₃₀ alkynylene; C₁-C₃₀ heteroalkylene, C₂-C₃₀ heteroalkenylene,C₂-C₃₀ heteroalkynylene, C₇-C₃₀ heteroalkylarylene, C₈-C₃₀heteroalkenylarylene, C₈-C₃₀ heteroalkynylarylene, C₇-C₃₀ alkylarylene,C₈-C₃₀ alkenylarylenc. C₈-C₃₀ alkynylarylene, and C₂-C₃₀ heteroarylene:and R⁹ and R¹⁰ are each independently selected from H, C₁-C₃₀ alkyl,C₁-C₃₀ heteroalkyl, C₂-C₃₀ alkenyl, C₂-C₃₀ alkyiryl, C₂-C₃₀hetemalkenyl, and C₂-C₃₀ heteroalkynyl: wherein said alkyl and alkylenecan be substituted with one or more of hydroxy, alkoxy, halogen, nitro,cyano, CO₂R, where R is defined above, phenyl, aryl heteroaryl,cycloalkyl, mercapto, or alkylthio.
 2. The biocompatible polymer ofclaim 1, wherein R¹ is C₁-C₄ alkylene.
 3. The biocompatible polymer ofclaim 2, wherein R¹is --CH₂CH₂—.
 4. The biocompatible polymer of claim1, wherein A¹ is carbonyl.
 5. The biocompatible polymer of claim 1,wherein n1 is zero and n2 is an average value between 0.5 and
 6. 6. Thebiocompatible polymer of claim 5, wherein n2 is an average value between1 and
 2. 7. The biocompatible polymer of claim 1, wherein said recurringunit is of formula:


8. The biocompatible polymer of claim 1, wherein said recurring unit isof formula:

wherein R³ is selected from the group consistimg of hydrogen and linearor branched C₁-C₃ alkyl.
 9. The biocompatible polymer of claim 8,wherein said recurring unit is of formula:


10. The biocompatible polymer of claim 9, wherein R is hydrogen ormethyl.
 11. The biocompatible polymer of claim 1, further comprising amacromeric recurring unit,
 12. A hydroxyacid-phenol compound of formula:

wherein y1 is 0, 1, 2, 3, or 4; X¹ is bromine (Br) or iodine (I):. X²and X³ are independently selected from O, S and NR, where R is H orlower alkyl; R¹ is selected from the group consisting of linear orbranched C₁-C₁₂ alkylene; A is selected from the group consisting oflinear or branched C₁-C₂₄ alkylene: R² is selected, from the groupconsisting of linear or branched C₁-C₂₄ alkylene; n1 and n2 areindependently numbers from 0 to 100; and are average values which can hefractional, where the sum of n1 and n2 is at least 1: p is zero or 1;and wherein said alkyl and alkylene can be substituted with one or moreof hydroxy, alkoxy, halogen, nitro, cyano, CO₂-lower alkyl phenyl, aryl,heteroaryl, cycloalkyl, mercapto, or alkylthio.
 13. Thehydroxyacid-phenol compound of claim 12, wherein n1 is zero and n2 is anaverage value of
 2. 14. The hydroxyacid-phenol compound of claim 12,wherein X¹═I and y1=2.
 15. The hydroxyacid-phenol compound of claim 12,wherein R¹ is —CH₂CH₂—.
 16. The hydroxyacid-phenol compound of claim 12,having the formula:


17. The hydroxyacid-phenol compound of claim 12 having the formula:

wherein R³ is selected from the group consisting of hydrogen and linearor branched C₁-C₂₃ alkyl.
 18. The hydroxyacid-phenol compound of claim17 has ing the formula:


19. The hydroxyacid-phenol compound of claim 18, wherein R³ is hydrogenor methyl,
 20. A polymer composition comprising a biocompatible polymeraccording to claim 1,
 21. A medical device comprising a biocompatiblepolymer according to claim
 1. 22. The medical device of claim 21,further comprising a biologically active compound,
 23. The medicaldevice of claim 22, wherein the biologically active compound isselected, from the group consisting of a chemotherapeutic agent, anon-steroidal anti-inflammatory, a steroidal anti-inflammatory, and awound healing agent.
 24. The medical device of claim 21, wherein themedical device is a stem.
 25. The biocompatible polymer of claim 1,further comprising a recurring unit of the formula:—[B-A¹-] wherein B is —O—((CHR)_(p)—O)_(p)—O)_(q)—; each R isindependently H or C₁ to C₃ alkyl; p and q are each independently aninteger in the range of from 1 to 100; and A¹ is as defined in claim 1,independently from any other A¹,
 26. The biocompatible polymer of claim25, wherein R is H and p is
 2. 27. The biocompatible polymer of claim 1,further comprising, as tyrosol recurring unit characterized by theformula:

wherein A¹ is as defined in claim
 1. independently from any other A¹/28. The biocompatible polymer of claim 1, further comprising aniodinated tyrosol recurring unit characterized by the formula:

wherein A¹ is as defined in claim 1, independently from any other A¹,29. The biocompatible polymer of claim 1, further comprising aniodinated recurring unit characterized by the formula:

wherein A¹ is as defined in claim 1, independently from any other A².30. The biocompatible polymer of claim 9, wherein n2 is greater thanzero and leis methyl and the subunit is derived from L-lactic acid. 31.The biocompatible polymer of claim 9, wherein n2 is greater than zeroand R³ is methyl and the subunit is derived from D-lactic acid.
 32. Thebiocompatible polymer of claim 9, wherein n2 is greater than zero and R³is methyl and the subunit is derived from D,L,-lactic acid,
 33. Thehydroxyacid-phenol compound of claim 18, wherein n2 is greater than zeroand R′is methyl and the subunit is derived from L-lactic acid.
 34. Thehydroxyacid-phenol compound of claim 18, wherein n2 is greater than zeroand Wis methyl and the subunit is derived from D-lactic acid.
 35. Thehydroxyacid-phenol compound of claim 18, wherein n2 is greater than zeroand itis methyl and the subunit is derived front DL-lactic acid.